EP2701632B1 - Systems and methods for determining intraocular lens power - Google Patents
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- EP2701632B1 EP2701632B1 EP12723552.1A EP12723552A EP2701632B1 EP 2701632 B1 EP2701632 B1 EP 2701632B1 EP 12723552 A EP12723552 A EP 12723552A EP 2701632 B1 EP2701632 B1 EP 2701632B1
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- 238000000034 method Methods 0.000 title claims description 28
- 230000004323 axial length Effects 0.000 claims description 20
- 230000002980 postoperative effect Effects 0.000 claims description 19
- 238000001356 surgical procedure Methods 0.000 claims description 19
- 230000003287 optical effect Effects 0.000 claims description 16
- 238000005259 measurement Methods 0.000 claims description 12
- 210000002159 anterior chamber Anatomy 0.000 claims description 7
- 230000001419 dependent effect Effects 0.000 claims 6
- 210000000695 crystalline len Anatomy 0.000 description 81
- 238000004364 calculation method Methods 0.000 description 17
- 210000004087 cornea Anatomy 0.000 description 6
- 230000004438 eyesight Effects 0.000 description 5
- 208000002177 Cataract Diseases 0.000 description 4
- 230000001886 ciliary effect Effects 0.000 description 4
- 230000036040 emmetropia Effects 0.000 description 4
- 210000003205 muscle Anatomy 0.000 description 4
- 210000001525 retina Anatomy 0.000 description 4
- 238000004422 calculation algorithm Methods 0.000 description 3
- 238000009472 formulation Methods 0.000 description 3
- 238000002513 implantation Methods 0.000 description 3
- 239000000203 mixture Substances 0.000 description 3
- 238000010276 construction Methods 0.000 description 2
- 239000007943 implant Substances 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 230000000704 physical effect Effects 0.000 description 2
- 208000029091 Refraction disease Diseases 0.000 description 1
- 230000004430 ametropia Effects 0.000 description 1
- 238000013459 approach Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000011156 evaluation Methods 0.000 description 1
- 238000013532 laser treatment Methods 0.000 description 1
- 238000012417 linear regression Methods 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 239000012528 membrane Substances 0.000 description 1
- 208000001491 myopia Diseases 0.000 description 1
- 238000005457 optimization Methods 0.000 description 1
- 238000010238 partial least squares regression Methods 0.000 description 1
- 230000004310 photopic vision Effects 0.000 description 1
- 210000001747 pupil Anatomy 0.000 description 1
- 208000014733 refractive error Diseases 0.000 description 1
- 230000002040 relaxant effect Effects 0.000 description 1
- 238000012552 review Methods 0.000 description 1
- 230000004296 scotopic vision Effects 0.000 description 1
- 238000007619 statistical method Methods 0.000 description 1
- 238000011282 treatment Methods 0.000 description 1
- 230000004304 visual acuity Effects 0.000 description 1
- 230000000007 visual effect Effects 0.000 description 1
- 230000004412 visual outcomes Effects 0.000 description 1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
- A61B3/0016—Operational features thereof
- A61B3/0025—Operational features thereof characterised by electronic signal processing, e.g. eye models
-
- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06F—ELECTRIC DIGITAL DATA PROCESSING
- G06F17/00—Digital computing or data processing equipment or methods, specially adapted for specific functions
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2240/00—Manufacturing or designing of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2240/001—Designing or manufacturing processes
- A61F2240/002—Designing or making customized prostheses
Definitions
- V L post AL - ( ACD pre +.5 LT ).
- the instructions of the system 300 will include elements of the method 300 and/or parameters and routines for performing calculations of one or more of Equations above.
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- Life Sciences & Earth Sciences (AREA)
- Ophthalmology & Optometry (AREA)
- Public Health (AREA)
- Animal Behavior & Ethology (AREA)
- Physics & Mathematics (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Veterinary Medicine (AREA)
- General Health & Medical Sciences (AREA)
- Molecular Biology (AREA)
- Theoretical Computer Science (AREA)
- Biophysics (AREA)
- Signal Processing (AREA)
- Medical Informatics (AREA)
- Cardiology (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Transplantation (AREA)
- Vascular Medicine (AREA)
- Surgery (AREA)
- Data Mining & Analysis (AREA)
- Mathematical Physics (AREA)
- Software Systems (AREA)
- General Engineering & Computer Science (AREA)
- General Physics & Mathematics (AREA)
- Databases & Information Systems (AREA)
- Prostheses (AREA)
Description
- The present invention relates generally to ocular surgical procedures involving implantable lenses, and more specifically to devices, systems and methods for the determination or selection of a lens power for providing emmetropic vision or, if chosen, a specific ametropic vision, taking into account various parameters of the eye.
- Intraocular Lenses (IOLs) may be used for restoring visual performance after a cataract or other ophthalmic procedure in which the natural crystalline lens is replaced with or supplemented by implantation of an IOL. Accurate determination of lens power is an important aspect in providing emmetropia, or a desired degree of ametropia. Measurements of the eye are typically made preoperatively and a lens power is selected based on correlations between the measured values and lens powers providing a desired refractive outcome.
- Over the years a number of intraocular lens power calculation formulas have been developed, for example, as discussed in the book published by SLACK Incorporated entitled Intraocular Lens Power Calculations, by H. John Shammas. These power formulas may be broadly characterized into at least two categories: theoretical formulas, which are based on a geometric optic, two-lens vergence formula; and regression formulas, which are based on regression formulas obtained by fitting data from a large patient database to an equation relating lens power to one or more parameters thought to correlate with lens power. While progress has been made in the accuracy of intraocular lens power calculation formulas to obtain better refractive outcomes, undesirable refractive outcomes due to improper intraocular lens power calculations still occur. Apart from the general desire for spectacle-free refractive outcomes, demands for more accurate lens power calculation have also increased due to the introduction of multifocal, as well as accommodating IOLs.
- Many of the current formula algorithms were derived by optical back-calculations to agree with a refractive outcome. In this manner they may be confounded with errors in all parameters used in the calculation, and the oversimplification of thin-lens theory. An evaluation of the sources of errors in lens power calculations was published by Sverker Norrby entitled "Sources of error in intraocular lens power calculation", Journal of Cataract and Refractive Surgery, Vol. 34, pp. 368-376, March 2008. In this paper, preoperative estimation of postoperative intraocular lens position was determined to be the largest contributor of error in the refractive outcome of cataract surgery, with an error contribution of 35%, relative to all error sources evaluated. Another publication by Olsen ("Calculation of intraocular lens power : a review." Acta Opthalmologica Scandinavica 2007;85:472-485) reports the same order of magnitude for the same source of error.
- In most, if not all of the current formula algorithms, there are a number of ocular parameters that are used in deriving an appropriate lens power for implantation into the eye. These parameters include axial length (AL), corneal radius (CR) or power (K), and anterior chamber depth prior to surgery (ACD pre), among others. In general, one or more of these parameters are used to provide the preoperative estimation of the postoperative effective lens position (ELP), which is related to the IOL's principal plane, although it may be modified depending on the surgeon through the optimization of the corresponding IOL constant. The ELP is then used in combination with one or more of these same parameters to provide an estimate of the correct lens power to provide a desired refractive outcome (typically emmetropia).
- For example, in the SRK/T method, the empirical calculation based on regressions is used to predict the ELP in the eye after surgery. Once that position is known, the IOL power to implant is calculated by simple paraxial optics, taking into account that the eye is a two lens system (cornea + IOL), focusing on the retina. This approach is based on Fyodorov's theoretical formula. However, as discussed above, calculating ELP is a large error source in this process. Accordingly, better systems and methods are needed that will allow reliable and accurate determination of an implanted lens' power.
- Embodiments of the present invention may be better understood from the following detailed description when read in conjunction with the accompanying drawings. Such embodiments, which are for illustrative purposes only, depict novel and non-obvious aspects of the invention. The drawings include the following figures:
-
Figure 1 is a cross-sectional view of a phakic eye containing a natural crystalline lens. -
Figure 2 is a cross-sectional view of a pseudophakic eye containing an intraocular lens. -
Figure 3 is a graph illustrating the predicted versus observed vitreous length, using the preoperative vitreous length, ACD and lens thickness as parameters. -
Figure 4 is a graph illustrating the predicted versus observed vitreous length, using the preoperative vitreous length and lens thickness as parameters. -
Figure 5 is a graph illustrating the post operative total power of the eye versus the preoperative vitreous length. -
Figure 6 is a flow chart of a method according to an embodiment of the present invention. -
Figure 7 is a graphical representation of the elements of computing system for selecting an ophthalmic lens according to an embodiment of the present invention. - The present invention generally provides devices, systems, and methods for selecting an optical power of an intraocular lens that will provide a predetermined refractive outcome. In many cases the desired outcome will be emmetropia, for example, so that the eye into which the lens is located has a visual acuity for distant objects that is at least 20/20 based on a Snellen chart.
- The following disclosure will be primarily directed to embodiments of the invention as they apply to implantable intraocular lenses; however, it is understood that other examples may be applied directly, or indirectly, to other types of ophthalmic lenses including, but not limited to, corneal implants, corneal surgical procedures such as LASIK or PRK, contact lenses, and other such devices. In some embodiments, various types of ophthalmic devices are combined, for example, an intraocular lens and a LASIK procedure may be used together to provide a predetermined visual outcome. Embodiments of the invention may also find particular use with multifocal or accommodating intraocular lenses, where a proper selection of lens power may be particularly important for achieving a desired refractive outcome.
- Embodiments of the invention may be understood by reference to
FIG. 1 , which is a cross-sectional view of a phakic eye with the natural crystalline lens, aneye 10 comprises aretina 12 that receives light in the form of an image that is produced by the combination of the optical powers of acornea 14 and a naturalcrystalline lens 16, both of which are generally disposed about an optical axis OA. As used herein, an "anterior direction" is in the direction generally toward thecornea 14, while a "posterior direction" is generally in the direction toward theretina 12. - The
natural lens 16 is contained within acapsular bag 20, which is a thin membrane that completely encloses thenatural lens 16 and is attached to aciliary muscle 22 viazonules 24. Aniris 26, disposed between thecornea 14 and thenatural lens 16, provides a variable pupil that dilates under lower lighting conditions (scotopic vision) and contracts under brighter lighting conditions (photopic vision). Theciliary muscle 22, via thezonules 24, controls the shape and position of thenatural lens 16, which allows theeye 10 to focus on both distant and near objects. Distant vision is provided when theciliary muscle 22 is relaxed, wherein thezonules 24 pull thenatural lens 16 so that thecapsular bag 20 is generally flatter and has a longer focal length (lower optical power). Near vision is provided as the ciliary muscle contracts, thereby relaxing thezonules 24 and allowing thenatural lens 16 to return to a more rounded, unstressed state that produces a shorter focal length (higher optical power). - The optical performance of the
eye 10 also depends on the spacing between thecornea 14 and thenatural lens 16, sometimes referred to as the anterior chamber depth prior to an ocular surgical procedure, ACD pre . As used herein, the "anterior chamber depth prior to surgery", "anterior chamber depth prior to an ocular surgical procedure", or "ACD pre", is defined as a distance between an apex of the anterior corneal surface and an apex of the anterior natural crystalline lens surface, prior to a surgery to replace the naturalcrystalline lens 16 with an intraocular lens. In some situations or cases, ACD pre may be defined or approximated as a distance between an apex of a cornea and an anterior surface of theiris 26. - Referring additionally to
FIG. 2 , which is a cross-sectional view of apseudophakic eye 10, the natural crystalline 16 lens has been replaced by anintraocular lens 100 according to an embodiment of the present invention. Theintraocular lens 100 comprises an optic 102 andhaptics 104, thehaptics 104 being generally configured to center the optic 102 within thecapsular bag 20. Numerous configurations ofhaptics 104 relative to optic 102 are well know within the art and embodiments of the present invention may be applied to any of these. - In order to calculate, determine, or estimate the power of an
intraocular lens 100 that is able to provide emmetropia or some other predetermined refractive outcome, various dimensions or measurements of theeye 10 are made prior to the surgical procedure. In addition to ACDpre, embodiments of the present invention also measure axial length AL, and/or natural lens thickness LT, as illustrated inFIG. 1 . From these measurements, VLpre , which is the preoperative vitreous length of the eye measured as the difference between the AL and the ACDpre plus LT can be ascertained. - Various formulations exist within the art that are used for calculation both of lens power and position of an intraocular lens after an ocular surgical procedure. These formulations generally comprise three steps:
- 1. Measure an eye;
- 2. Estimate the postoperative position of an intraocular lens;
- 3. Perform a lens power calculation based on the estimate and/or eye measurements.
- Although all three steps are important, the second step of estimating the postoperative position of an intraocular lens may benefit most from improvements in the current state of the measurement arts. For example, in the Norrby reference cited above, preoperative estimation of the ELP was determined to be the largest contributor of error in the refractive outcome of cataract surgery, with an error contribution of 35%, relative to all error sources evaluated. In addition, the correct determination of the actual lens position is even more important because it is a real distance, and not a manufactured parameter that may be modified to optimize outcomes.
- Furthermore, the inventors have found that the combined measurements of VLpre, ACDpre, and LT are highly predictive in calculating the postoperative vitreous length, from which the position of the implanted
intraocular lens 100 or optic 102 can be derived if its thickness is known. The calculated position will generally be given herein in terms of the "postoperative vitreous length" (VLpost ), which is defined herein as the distance from the back of the IOL to the retina. - In certain embodiments, a highly predictive formulation of VLpost is calculated based on the following mathematical relationship which includes VLpre. ACDpre, and LT:
where VLpre is the preoperative vitreous length of the eye measured as the difference between the AL and the ACDpre plus LT. ACD pre is the anterior chamber depth prior to an ocular surgical procedure as measured from the anterior corneal surface to the anterior lens surface, LT is the lens thickness, and C1-C4 are constants, that may depend on the IOL model. AL, ACD pre and LT may be measured with, for example the AC Master or other biometer and VLpre can be then be calculated from these measurements. - By way of non-limiting example, in certain 3 piece intraocular lens embodiments, constants for VLpost may be as follows: C1 = -.901; C2 = 0.982; C3 = 0.309; and C4 = 0.545.
- This prediction was checked post-operatively by measuring the ACDpost with the AC master, and then calculating the actual VLpost as equaling AL - (ACDpost + IOLct ) where IOLct is the center thickness of the implanted IOL. This illustrated embodiment was found to be highly predictive of VLpost with r 2 = 0.978, as illustrated in
Figure 3 . - In some embodiments, AL may be used rather than VLpre according to the following mathematical relationship: VL post = AL - (ACDpre +.5LT). AL may be measured, for example, with the IOL Master. This illustrated embodiment was found to be highly predictive of VLpost with r 2 = 0.86 as seen in
Figure 4 . - Another embodiment uses AL rather than VLpre according to the following mathematical relationship: VLpost = C1 + C2 * AL + C3 * ACD pre + C4 * LT where constants in certain 1 piece intraocular lens embodiments may be as follows: C1 = -2.042; C2 = 0.944; C3 = 0.396; and C4 = 0.203. This illustrated embodiment was found to be highly predictive of VLpost with r2 = 0.93. By way of non-limiting example, in certain 3 piece intraocular lens embodiments, constants for VLpost may be as follows: C1 = -.902; C2 = 0.983; C3 = 0.673; and C4 = 0.437. This illustrated embodiment was also found to be highly predictive of VLpost with r2 = 0.98.
- In some embodiments, one or more of the measured variables may be left out. For example, the measurement of ACDpre may be left out and the coefficients for LT and VLpre may be evaluated according to the following mathematical relationship:
- As detailed in
Figure 5 , the preoperative vitreous length was also found to be a good predictor for the post operative total power of the eye with r 2 = 0.71. - Each of the aforementioned constant values are preferably within plus or minus 20 percent of the nominal value thereof, or even more preferably within plus or minus 10 percent of the nominal value thereof.
- Referring to
FIG. 6 , in certain embodiments, amethod 200 for selecting theintraocular lens 100 or an optical power thereof comprises anelement 205 of determining one or more physical and/or optical properties of theeye 100. Themethod 200 also comprises anelement 210 of calculating a position of theintraocular lens 100 or the optic 102 after an ocular surgical procedure as detailed above. Themethod 200 additionally comprises anelement 215 of calculating or estimating an optical power of theintraocular lens 100 suitable for providing a predetermined refractive outcome. - With reference to
FIGS. 1 and 2 ,element 205 comprises measuring ACDpre, AL, and/or LT of theeye 10 and then calculating VLpre from these measurements, as previously indicated. In addition, other various physical properties of the eye may also be measured or estimated (e.g., a refractive index of a material of the eye, and the like) and/or information of the patient or IOL collected (e.g., age, sex, which eye, IOL model, IOL optic and/or haptic dimensions and thickness, or the like). - The
element 210 of themethod 200 comprises calculating a position of theintraocular lens 100 or the optic 102 after an ocular surgical procedure. With reference toFIGS. 1 and 2 , the calculated position of theintraocular lens 100 is based on measured or calculated values of VLpre, ACDpre, AL, and/or LT of theeye 10. These values may be used in one or more of the above equations to calculate the lens position. In certain embodiments, the constants are selected using regression routine, for example, based on a multiple linear regression (MLR) analysis or a partial least squares (PLS) regression analysis, which may be run for different IOL models. - The
method 300 may be incorporated with one or more methods of inserting a lens within the individual eyes of the population. Such methods may also comprise making postoperative measurements of the eyes in the population to determine the postoperative position of the lens for each eye within the population and/or to use the information to further refine the mathematical modes defined by the equations above. Additionally or alternatively, such methods may further comprise conducting a statistical analysis of each measured or derived characteristic to determine (1) a correlation between the calculated postoperative lens position and the measured or derived characteristic(s) and/or (2) to determine coefficient value for an equation containing the measured or derived characteristic(s) as variables, the equation configured for calculating a postoperative lens position within an eye per IOL model. - Referring to
FIG. 6 , in certain embodiments, acomputer system 300 for calculating a postoperative lens position within an eye and/or for selecting an ophthalmic lens or an optical power thereof comprises aprocessor 302 and a computerreadable memory 304 coupled to theprocessor 302. The computerreadable memory 304 has stored therein an array of orderedvalues 308 and sequences ofinstructions 310 which, when executed by theprocessor 302, cause theprocessor 302 to calculate a postoperative lens position within an eye and/or for selecting an ophthalmic lens or an optical power thereof. The array of orderedvalues 308 may comprise, for example, one or more ocular dimensions of an eye or plurality of eyes from a database, a desired refractive outcome, parameters of an eye model based on one or more characteristics of at least one eye, and data related to an IOL or set of IOLs such as a power, an aspheric profile, and/or a lens plane. In some embodiments, the sequence ofinstructions 310 includes determining a position of an IOL, performing one or more calculations to determine a predicted refractive outcome based on an eye model and a ray tracing algorithm, comparing a predicted refractive outcome to a desired refractive outcome, and based on the comparison, repeating the calculation with an IOL having at least one of a different power and/or a different IOL location. - The
computer system 300 may be a general purpose desktop or laptop computer or may comprise hardware specifically configured performing the desired calculations. In some embodiments, thecomputer system 300 is configured to be electronically coupled to another device such as a phacoemulsification console or one or more instruments for obtaining measurements of an eye or a plurality of eyes. In other embodiments, thecomputer system 300 is a handheld device that may be adapted to be electronically coupled to one of the devices just listed. In yet other embodiments, thecomputer system 300 is, or is part of, refractive planner configured to provide one or more suitable intraocular lenses for implantation based on physical, structural, and/or geometric characteristics of an eye, and based on other characteristics of a patient or patient history, such as the age of a patient, medical history, history of ocular procedures, life preferences, and the like. - Generally, the instructions of the
system 300 will include elements of themethod 300 and/or parameters and routines for performing calculations of one or more of Equations above. - In certain embodiments, the
system 300 includes or is part a phacoemulsification system, laser treatment system, optical diagnostic instrument (e.g, autorefractor, aberrometer, and/or corneal topographer, or the like). For example, the computerreadable memory 304 may additionally contain instructions for controlling the handpiece of a phacoemulsification system or similar surgical system. Additionally or alternatively, the computerreadable memory 304 may additionally contain instructions for controlling or exchanging data with an autorefractor, aberrometer, and/or corneal topographer, or the like, - In some embodiments, the
system 300 includes or is part of a refractive planner. The refractive planner may be a system for determining one or more treatment options for a subject based on such parameters as patient age, family history, vision preferences (e.g., near, intermediate, distant vision), activity type/level, past surgical procedures. - The above presents a description of the best mode contemplated of carrying out the present invention, and of the manner and process of making and using it, in such full, clear, concise, and exact terms as to enable any person skilled in the art to which it pertains to make and use this invention. This invention is, however, susceptible to modifications and alternate constructions from that discussed above which are fully equivalent. Consequently, it is not the intention to limit this invention to the particular embodiments disclosed. On the contrary, the intention is to cover modifications and alternate constructions coming within the scope of the invention as generally expressed by the following claims, which particularly point out and distinctly claim the subject matter of the invention.
Claims (14)
- A computer-implemented method of selecting an optical power of an intraocular lens, comprising:determining a value for the postoperative vitreous length of an eye from preoperative measurements of the preoperative vitreous length (VLpre), anterior chamber depth prior to surgery (ACDpre), axial length (AL), and/or natural lens thickness (LT);calculating an optical power of the intraocular lens based on the postoperative vitreous length suitable for providing a predetermined refractive outcome.
- The method of claim 1, wherein the postoperative vitreous length is a dependent variable VLpost and the mathematical relationship is:
wherein C1 is a constant with a nominal value of -0.901, C2 is a constant with a nominal value of 0.982, C3 is a constant with a nominal value of 0.309, and C4 is a constant with a nominal value of 0.545, each of the constants having a value that is within plus or minus 20 percent of the nominal value thereof. - The method of claim 2, wherein each of the constants has a value that is within plus or minus 10 percent of the nominal value thereof.
- The method of claim 2, wherein each of the constants has a value that is within plus or minus 5 percent of the nominal value thereof.
- The method of claim 1, wherein the postoperative vitreous length is a dependent variable VLpost and the mathematical relationship is:
wherein C1 is a constant with a nominal value of 1.63, C2 is a constant with a nominal value of 0.912, and C3 is a constant with a nominal value of 0.448, each of the constants having a value that is within plus or minus 20 percent of the nominal value thereof. - The method of claim 6, wherein each of the constants has a value that is within plus or minus 10 percent of the nominal value thereof.
- The method of claim 6, wherein each of the constants has a value that is within plus or minus 5 percent of the nominal value thereof.
- A system for providing an intraocular lens, the system comprising:a processor; anda computer readable memory configured to communicate with the processor, the memory having stored therein:an array of ordered values, including at least one of:one or more ocular dimensions, the ocular dimensions including preoperative vitreous length (VLpre), anterior chamber depth prior to surgery (ACDpre), axial length (AL), and/or natural lens thickness (LT);a predetermined refractive outcome;a sequence of instructions which, when executed by the processor, cause the processor to select an intraocular lens or an intraocular lens power, the sequence of instructions including:calculating the VLpost;calculating an optical power of the intraocular lens suitable for providing the predetermined refractive outcome.
- The system of claim 9, wherein VLpost is a dependent variable and the mathematical relationship is:
wherein C1 is a constant with a nominal value of -0.901, C2 is a constant with a nominal value of 0.982, C3 is a constant with a nominal value of 0.309, and C4 is a constant with a nominal value of 0.545, each of the constants having a value that is within plus or minus 20 percent of the nominal value thereof. - The system of claim 10, wherein each of the constants has a value that is within plus or minus 10 percent of the nominal value thereof, wherein preferably each of the constants has a value that is within plus or minus 5 percent of the nominal value thereof.
- The system of claim 11, wherein VLpost is a dependent variable and the mathematical relationship is:
wherein C1 is a constant with a nominal value of 1.63, C2 is a constant with a nominal value of 0.912, and C3 is a constant with a nominal value of 0.448, each of the constants having a value that is within plus or minus 20 percent of the nominal value thereof. - The system of claim 13, wherein each of the constants has a value that is within plus or minus 10 percent of the nominal value thereof, wherein preferably each of the constants has a value that is within plus or minus 5 percent of the nominal value thereof.
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US201161480589P | 2011-04-29 | 2011-04-29 | |
PCT/US2012/035539 WO2012149383A1 (en) | 2011-04-29 | 2012-04-27 | Systems and methods for determining intraocular lens power |
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EP (1) | EP2701632B1 (en) |
AU (1) | AU2012249481B2 (en) |
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WO2012092584A1 (en) | 2010-12-30 | 2012-07-05 | AMO Wavefront Sciences LLC. | Improved treatment planning method and system for controlling laser refractive surgery |
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US10582847B2 (en) | 2010-12-30 | 2020-03-10 | Amo Wavefront Sciences, Llc | Method and system for eye measurements and cataract surgery planning using vector function derived from prior surgeries |
US10582846B2 (en) | 2010-12-30 | 2020-03-10 | Amo Wavefront Sciences, Llc | Method and system for eye measurements and cataract surgery planning using vector function derived from prior surgeries |
AU2012322746B2 (en) | 2011-10-14 | 2017-05-04 | Amo Groningen B.V. | Apparatus, system and method to account for spherical aberration at the iris plane in the design of an intraocular lens |
DE102013002293A1 (en) * | 2013-02-08 | 2014-08-14 | Carl Zeiss Meditec Ag | Eye surgery systems and methods for inserting intro-cular lenses |
JP6568873B2 (en) * | 2014-02-03 | 2019-08-28 | シャマス,ハンナ | System and method for determining intraocular lens power |
CA2991484A1 (en) | 2015-07-27 | 2017-02-02 | Amo Wavefront Sciences Llc | Optical imaging and measurement systems and methods for cataract surgery and treatment planning |
AU2017352030B2 (en) | 2016-10-25 | 2023-03-23 | Amo Groningen B.V. | Realistic eye models to design and evaluate intraocular lenses for a large field of view |
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US11890184B2 (en) * | 2017-09-29 | 2024-02-06 | John Gregory LADAS | Systems, apparatuses, and methods for intraocular lens selection using artificial intelligence |
WO2019106067A1 (en) | 2017-11-30 | 2019-06-06 | Amo Groningen B.V. | Intraocular lenses that improve post-surgical spectacle independent and methods of manufacturing thereof |
ES2899735T3 (en) * | 2018-01-05 | 2022-03-14 | Alcon Inc | Systems and methods for the selection of an intraocular lens |
CN109683311B (en) * | 2019-01-14 | 2021-02-02 | 杭州明视康眼科医院有限公司 | Diopter calculation method for intraocular lens |
CN111166530B (en) * | 2020-01-03 | 2022-09-06 | 中山大学中山眼科中心 | Method for predicting postoperative position of artificial lens |
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US5092880A (en) * | 1988-10-21 | 1992-03-03 | Genjiro Ohmi | Method of determining the astigmatic power and the power for an intraocular lens, for a toric intraocular lens |
WO2010064150A2 (en) | 2008-04-04 | 2010-06-10 | Amo Regional Holdings | Systems and methods for determing intraocular lens power |
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CA2834564A1 (en) | 2012-11-01 |
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